Method and apparatus for detecting the respiratory activity of a person

Abstract

A method and a device are provided for detecting the respiratory activity of a person and for controlling the time progression of breathing gas pressure, especially in accordance with physical parameters and considering parameters indicating the momentary physiological condition of the breathing person. The device for detecting the respiratory activity of a person has at least one sensor that provides a first signal indicating the breathing gas flow, wherein at least one signal processing device is provided for processing the first signal. The signal processing device is configured in such a way that said device determines a reference-relation on the basis of the first signal detected during a first time interval. On the basis thereof, the device determines a correlation-relation between the reference-relation and the first signal. The device generates an output signal indicating the respiratory activity and/or the physiological condition of the breathing person by considering at least the correlation-relation.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. application Ser. No. 11/454,835, filed Jun. 19, 2006, now U.S. Pat. No. 7,934,500, which is a continuation of U.S. application Ser. No. 10/070,346, filed Jun. 21, 2002, now U.S. Pat. No. 7,089,936, which claims the benefit of PCT Application Serial No. PCT/EP01/07574, filed Jul. 2, 2001, which in turn claims the benefit of German Application Serial No. DE 100 31 079.6, filed Jun. 30, 2000, each incorporated herein by reference in its entirety.

FIELD OF TECHNOLOGY

The present invention is directed to a device for the detection of the respiratory activity of a person as well as for controlling the time related course of respiratory gas pressure particularly in accordance with physical parameters and parameters indicative with respect to the actual physical condition of a respirating person. The present invention may be applied particularly in the field of sleep medicine for diagnosing and/or treating sleep related breathing disorders by positive pressure respiration (CPAP-Therapy). Further, the present invention addresses a method for controlling a respiratory gas pressure in connection with excess-pressure respiratory gas supply.

BACKGROUND OF TECHNOLOGY

CPAP-Therapy (Continuously Positive Airways Pressure-Therapy) affords prevention of sleep related breathing disorders in a physiologically well accepted manner.

By means of respiratory gas supplied at a defined elevated pressure level above ambient pressure a pneumatic splinting of the upper airways may be achieved to effectively prevent potential obstructions in this region—or to afford sufficient Oxygen supply towards the patient in case of temporarily contraction of said upper airways. To achieve high physiological acceptability it is usually envisaged to adjust a low respiratory pressure level affording sufficient pneumatic splinting of the upper airways. However, it has become evident that aforesaid low respiratory pressure level is subject to significant variations. Experiments have been made by using so called AUTO-CPAP devices which for example automatically increase the therapy pressure upon occurrence of snoring sounds, to take these variations in required CPAP-pressure into account. Further CPAP-devices are known for detecting the time related course of the breathing gas flow and analyzing same with respect to features indicative with respect to airway obstructions. In case of such airway obstructions an increase of the therapy-pressure is temporarily administered.

Also there are known Auto-CPAP devices determining the present physiological condition of a patient by means of pressure pulses applied to the respiratory gas supplied via a breathing gas conduit wherein for example on the basis of an impedance detection the present degree of obstruction may be concluded.

From EP 0 612 257 B1 there is known a system for generation of continuously positive respiratory gas pressure, which system changes the pressure level of the gas supplied to the patient in a defined manner, and which analyses changes of the airflow profile that may go along therewith.

With respect to the pressure control concepts applied so far for automatic patient-related adjustment of the breathing gas pressure there exists a problem in that the changes of the respiratory pressure administered thereby are not universally accepted by the respective patients. Further there exists a problem in that the known auto-CPAP systems start to react on significant breathing disorders only.

SUMMARY OF TECHNOLOGY

It is an object of the present invention to provide a device for the detection of the respiratory activity as well as for the provision of physical parameters during administration of a respiratory gas to a patient that allows a precise determination of the physiological state of the patient.

According to the present invention this object is performed by a device for detecting breathing activity of a person comprising at least one means for supplying a first signal indicative with respect to breathing gas flow; and at least one signal processing means for processing said first signal, wherein said signal processing means being construed so as to generate a reference relation on the basis of said first signal detected over a first time period, and a correlation-relation between said reference-relation and said first signal, said signal processing means being further construed so as to generate on the basis of an observation of at least said correlation-relation an output signal which is indicative with respect to the breathing activity, in particular classifying same.

This affords in an advantageous manner an extremely exact classification of the respiratory activity of the respirating person and, based thereon, meeting the patients physiological state, a precise setting of the respiratory pressure in a convenient manner without disturbing the natural sleep behaviour. The pressure control based on the precise classification or detection of the respiratory activity provides a clearly improved acceptance of therapy and allows a far sighted adjustment of the breathing gas pressure, which may prevent occurrence of potentially occurring airway obstructions with a high likelihood.

On the basis of the determination-concept according to the present invention it might be possible in an advantageous manner to ensure that a patient-specific setting of the breathing gas pressure adjusted by a respective CPAP-device is achieved with high reliability and without particular diagnostic efforts. On the basis of the determination concept according to the present invention it is further enabled to dispense from active variation of the breathing gas pressure as it was so far necessary for the supervision of the physiological state, and to determine the physiological state of the patient without arbitrarily adjusted pressure experiments.

According to a preferred embodiment of the present invention, the length of a first time period for determining the reference relation is determined so as to extend over at least two respiration cycles. It is possible to define the generation of the reference relation via a criteria-array. This criteria-array preferably includes a plurality of entries by which it is determined how the reference relation is generated from the first and second detected signals. It is possible for example to determine certain features of the reference relation by processing said first and second signals over a period which exceeds a shorter observation period for setting other features of said reference relation.

According to a particularly preferred embodiment of the present invention there is provided at least one filter-means for filtering the first and/or second signal with respect to a predetermined frequency-range. This affords to extensive suppression of certain detection-related noise impacts.

According to a further preferred embodiment of the present invention the signal processing means includes at least one smoothing means for smoothing said reference relation by application of predetermined smoothing criteria. According to a preferred embodiment, said smoothing criteria are set adaptively. It is also possible to select preset smoothing criteria for certain respiratory states, or to adapt the smoothing criteria to the detected respiratory state.

Preferably the parameters of the filter means are adaptively adjusted. The adaptation behaviour may preferably determined by input of respective parameters.

According to a particularly preferred embodiment of the present invention at least one of the aforementioned smoothing means is construed in such a manner that same effects smoothing on the basis of statistic methods.

The generation of output signals which are indicative with respect to the respiratory activity by means of said signal processing means is carried out in accordance with a preferred embodiment of the invention on the basis of a threshold observation. For this a threshold observation means processing threshold criteria in particular zero-crossings is preferably integrated into the signal processing means. Preferably, the signal processing means further includes counter means for counting accomplishment of predetermined criteria within a set time period. The time periods are preferably variably adapted to the present respiratory state.

The detection of signals indicative with respect to the breathing gas pressure may be carried out for example by means of a pressure sensor which is integrated into a respective CPAP-device and which detects for example via a sensing tube the static pressure within a region of a breathing mask applied to a patient. The signals indicative with respect to the breathing gas flow may be determined for example via a sensing shield arrangement provided in a breathing gas supply path.

By means of the device proposed according to the invention or on the basis of the analysis procedure carried out by said device a robust detection of each respiratory cycle of the respirating person is accomplished. In an advantageous manner the transition from the inspiratory phase into the expiratory phase happens via a characteristic flank on the basis of which a secure detection of each breathing cycle is enabled. In a preferred manner the first derivation in time is estimated. The local extremes of the estimated first derivation of the flow-function correspond to the maximum inclination of the respiratory flow during transition between inspiration and expiration. Beginning in the expiration phase the starting point of Inspiration is detected in that a search through the preceding extreme of the estimated second derivation is carried out. Further preferred embodiments of the invention are subject of the dependent claims.

The length of the first time period is preferably set so as to extend over at least two breathing cycles. Preferably a second means is provided for provision of a second signal indicative with respect to the dynamic and/or static pressure of the respiratory gas. In a preferred manner there is provided at least one filter means for filtering or damping the first and/or second signals.

The signal processing means preferably includes a smoothing means, for smoothing the reference relation by use of selected smoothing criteria. Said smoothing criteria are preferably adaptively changed. The signal processing means preferably includes a smoothing means for smoothing or damping said reference relation.

At least one of said smoothing means is preferably construed so as to effect smoothing on the basis of statistical solution-statements. The signal processing means preferably includes a threshold consideration means for evaluating said correlation-relation with respect to threshold criteria in particular zero crossing. The signal processing means preferably includes a counting means for counting performance of predetermined criteria within a preset period of time. The filter- and/or smoothing parameters are preferably adaptively fitted.

The object of the present invention as mentioned at the beginning is further solved by a device for supplying respiratory gas to a patient at excess-pressure via a feeding means for feeding said respiratory gas and a detection means for detecting at least the breathing gas pressure and/or the breathing gas flow, characterized by a signal processing means generating a reference relation on the basis of the detected signals and which is setting the breathing gas pressure on the basis of a correlation between said reference relation and the present breathing patterns.

The object mentioned at the beginning is further also solved by a method for controlling the respiratory gas pressure during CPAP-therapy, by detecting signals indicative with respect to the breathing gas pressure and the breathing gas flow, wherein on the basis of the time related dynamic of the measuring values of pressure and respiratory gas flow the presence and/or degree of a flow limitation is detected and the breathing gas pressure is controlled accordingly.

In one embodiment, the time-points of the beginning of Inspiration- and/or Expiration are determined in consideration of the inclination of a curvature portion of the gas flow by using statistic smoothing methods and wherein a significant variation of the distance between the ends of Inspiration- or Expiration is determined with respect to a number of subsequent breathing cycles.

In a advantageous manner irregularities within the breathing gas flow are detected by comparing the present breath with timely preceding breathings by application of statistical dependency measurements Preferably correlation-coefficients and/or mutual-informations are detected as measurements of dependency.

Preferably a correlation relation between a reference function and a present breathing flow is generated, wherein in case of to little statistical dependency between the present breath and the timely preceding breath the respiratory pressure is adjusted accordingly.

Preferably groups of breathings are standardized via affine transformation wherein the average curvature of the standardized breath is used for detection of probably existing flow limitations.

Further the object mentioned at the beginning is also solved by a method for controlling the breathing gas supply pressure during CPAP-therapy by detection of the sleeping position of the patient, in particular the head-position, and/or torsi-position or neck-torsion-degree and wherein the respiratory target pressure and/or the pressure control characteristic of the breathing gas supply is set in dependency of those detections.

According to a further aspect of the present invention the object mentioned at the beginning is solved by a method for controlling the breathing gas supply during CPAP-therapy including detection of a signal indicative with respect to breathing gas flow, and subjecting this signal a correlation-analysis on the basis of an adaptively actualized reference function, wherein on the basis of the results of the correlation analysis the physiological state of the patient is typified, wherein with respect to the control of the respiratory gas pressure, in particular with respect to setting a respiratory target pressure, the control characteristic of a respiratory gas pressure control means is adapted.

Preferably there are provided several pressure control modes adapted for selected sleep-stages of the patient. The sleeping position of the patient, in particular the head- and/or torsi-position, and/or the neck torsion degree are preferably detected in association herewith and the breathing gas target pressure and/or the pressure control characteristic of supplying respiratory gas is set in consideration of these detections also.

Further the object mentioned at the beginning is also performed by a method for controlling the supply of respiratory gas pressure during CPAP-therapy, including detection of a first signal indicative with respect to breathing gas flow, wherein this signal subjected to a correlation analysis based on an adaptively actualized reference function, wherein on the basis of the results of said correlation analysis a physiological state of the patient is typified, wherein in dependency of the result of typification the breathing gas pressure control is adjusted in such a manner, that same adjusts substantially equal static respiratory gas pressure values for inspiration and expiration within a mask region, —or different mask pressure values for inspiration and expiration (bilevel-mode).

BRIEF DESCRIPTION OF THE DRAWINGS

Further details and features will be apparent from the following description with reference to the drawings in which:

FIG. 1 shows (top) a data-portion of a flow graph of a patient during NREM2; (middle) a high vertical line indicating the end of inspiration, a low line indicating the start of inspiration; (bottom) the first derivation in time of the flow-graph on the basis of which the end and the beginning of inspiration may be detected

FIG. 2 shows (top) a data portion of a flow graph of a patient during NREM 2; (middle) the last breathing cycle of the data sequence above selected as reference relation for the breathing pattern; (bottom) correlation between the data portion above (reference relation) and the flow pattern in the midst;

FIG. 3 shows (top) a data portion of a flow graph of a patient during NREM2; (bottom) the average difference of the maxima of correlation from the value 1;

FIG. 4 shows (top) a data portion of the flow graph of a patient during REM; (bottom) average difference of the maxima of correlation from the value 1;

FIG. 5 shows (top) a data portion of the flow graph of a patient; (middle) associated CPAP-pressure graph; (bottom) variance of the CPAP signal per breathing cycle.

FIG. 6 is a schematic view of a device according to an embodiment of the present invention.

DETAILED DESCRIPTION OF ILLUSTRATED EXAMPLES

In FIG. 1 the top graph displays 45 seconds of a flow graph of a patient at NREM2-sleep stage. The lower graph of this figure shows an estimated first derivation of the flow graph. Between both graphs the hereby automatically detected transition points are indicated by vertical lines.

FIG. 6 is a schematic view of a device 10 constructed according to an embodiment of the present invention. Device 10 can be used to carry out the processing described below in relation to FIGS. 1-5. Device 10 includes a flow generator 15, a patient interface 20, e.g., a breathing mask, and a breathing gas conduit 25 to deliver pressurized gas from the flow generator 15 to the patient interface 20. Flow generator 15 typically includes a detector 30 to produce a signal relating to breathing gas pressure (e.g., via a pressure sensor) and/or breathing gas flow (e.g., via a flow sensor or meter). Flow generator 15 includes a processor 40, e.g., in the form of a CPU, to receive input signals from the detector 30. Processor 40 is adapted to generate a reference-relation on the basis of the detector signal to adjust the breathing gas pressure on the basis of a correlation-relation between the reference-relation and a prevailing breathing pattern of the patient.

For differentiation between stable and non-stable respiration, a measurement of similarity of a plurality of successive breathing cycles is considered. The height of a cross-correlation-function is an appropriate measurement for the similarity of the present breathing cycle with preceding breathing cycles. The top graph shown in FIG. 1 thereby illustrates the breathing gas flow of a patient during NREM2 sleep stage. The high vertical line of the middle graph indicates the end of inspiration, the lower vertical line of the middle graph indicates the end of expiration. The first derivation of the flow graph which allows detection of the end and the beginning of inspiration is illustrated as the lower graph. Because of the different extrema of the first derivation of the flow graph it is possible to reliably distinguish between individual breathing phases.

The FIG. 2 graph illustrates as an example a 50-second portion of respiratory flow of a patient during NREM 2. The middle graph is a selected breathing cycle. The lower graph illustrates the correlation between the data sequence (top graph) and said selected breathing cycle. The correlation graph assumes values between 1 and −1, wherein the correlation assumes the value 1 in case that both breathing cycles correspond to each other exactly, —and the correlation assumes the value −1 when the graphs are correlated negative i.e. a top section of breathing pattern exactly meets a valley section of the analyzed data portion.

On the basis of the correlation graph it is at first evident whether respiration is regular and at second whether breaths are missed completely. In case where successive breathing cycles are similar the graph of correlation will have a periodic course with local maxima close to 1 and local minima close to −1.

With respect to the correlation graph illustrated in FIG. 2 the difference to the value 1 is calculated at each local maxima, wherein all of the thus obtained values are averaged. This average value between 0 and 1 may be used as a measurement in how far the breathing pattern corresponds to the preceding breathing cycles.

In FIG. 3 the top graph illustrates the flow graph of a patient during NREM 2 sleep stage. The lower data sequence illustrates the average difference of the maxima of correlation to the value 1.

FIG. 4 basically corresponds to FIG. 3 however the flow graph here results from REM-sleep stage. The comparison of the average maxima of correlation according to FIGS. 3 and 4 shows that the average difference of the maxima of correlation to 1 in REM sleep stage is clearly greater.

The following table illustrates which groups of respiratory states could be differenciated on the basis of the measurement of similarity as set forth above.

stable respiration               non stable respiration

silent regular respiration       irregular respiration during REM
respiration with associated snoring obstructive apnea
mouth breathing                  awake respiration
Periodic breathing with flow limitation Cheyne Stoke respiration
dampened respiratory flow signal

Detection of Snoring

The detection of snoring may be effected according to a preferred embodiment of the invention on the basis of the variance of the CPAP-pressure within a breathing cycle. In FIG. 5 the top graph illustrates a portion of a respiratory flow signal, there under there is illustrated the corresponding CPAP-pressure. The graph bottom illustrates the variance of the CPAP-pressure per breath. Said variance clearly increases when the CPAP-Signal is varied due to patients snoring.

Further Parameters of Discernment

The reliable detection of the transition points for beginning and end of inspiration on the basis of the concept according to the present invention allows to retrieve further significant features for distinguishing of breathing states. Particular advantageously retrievable indications are the time of inspiration, the time of expiration, the maximum flow during inspiration, the maximum flow during expiration, the volume of inspiration and the volume of expiration.

Mouth Breathing

artefacts due to mouth-breathing may be reliably detected since in that case a negative correlation is existing. Obstructive apneas might be detected also in that certain peaks of correlation occur in a clearly weakened manner—or are completely missing in the regular case.

Flow Limited Breathing

On the basis of the concept underlying the present invention a flow limited breathing may be made out via the volume of inspiration or the relative change of the maximum inspiratory flow, in as far as inspiration is flow limited. If the approximate moments for beginning and end of inspiration are known it is possible to determine the moment of maximum inspiration. If this moment is placed in the first half of inspiration the presence of a flow limited inspiration may be assumed with high statistical likelihood and a respective correction of the respiratory pressure may be administered.

Cheyne Stoke Respiration

A periodic course of respiration showing periodic course of the inspiratory volume is characterizing Cheyne Stoke respiration which is thus distinguishable from other non stable breathing patterns.

Surveillance of the Detected Breaths

In a quite advantageously manner the correlation curve may be used for surveillance of the detected moments of beginning and end of inspiration, since a local maxima in the correlation graph is representing with high statistical safety a feature of a breath.

On the basis of the concept of analysis underlying the device according to the present invention it is possible to detect individual breath with high statistical likelihood and to make far reaching conclusions with respect to the present condition of the patient. Via the thus obtained detections it will become possible to adjust the therapy pressure in a predictive manner and with comparatively small changing-gradients in line with the physiological needs of the patient. This affords to a high acceptance of therapy.

Claims

1. A device for detecting a person's breathing activity and/or physiological condition, comprising:

a flow sensor configured to generate a first signal indicative of breathing gas flow over at least two breathing cycles; and

at least one processor configured to:

designate a limited portion of the first signal as a reference signal,

compare the reference signal with at least a portion of the first signal,

generate, based on the comparison, an output signal indicative of the breathing activity and/or the physiological condition of the person, and

mathematically correlate the reference signal with the first signal as the comparison,

wherein the mathematical correlation results in values between −1 and 1.

2. The device of claim 1, wherein the at least one processor is further configured to determine whether successive breathing cycles are similar by determining whether a graph of the mathematical correlation in corresponding portions has a similar periodicity, and whether in the corresponding portions local maxima are close to 1 and local minima are close to −1.

3. The device of claim 1, wherein the at least one processor is further configured to recognize whether the person's respiration is regular.

4. The device of claim 1, wherein the at least one processor is further configured to recognize whether the person's breaths are missed completely.

5. The device of claim 1, wherein the at least one processor is further configured to:

generate a signal corresponding to the first derivative of the first signal,

identify local maxima and minima of the signal corresponding to the first derivative of the first signal,

recognize transitions between inspiration and expiration with reference to the local maxima and minima, and

distinguish between individual breathing phases in accordance with the recognized transitions.

6. The device of claim 1, wherein the at least one processor is further configured to cause a flow generator to adjust an amount of pressure provided to the person in dependence on the output signal.

7. The device of claim 1, wherein the first signal extends over at least three breathing cycles, and wherein the reference signal corresponds to at least two breathing cycles.

8. The device of claim 7, wherein the reference signal corresponds to exactly two breathing cycles.

9. The device of claim 1, further comprising a filter configured to alter the first signal by removing or suppressing a predetermined frequency range therein.

10. The device of claim 1, wherein the at least one processor is further configured to smooth the reference signal in accordance with smoothing criteria.

11. The device of claim 10, wherein the smoothing criteria are adaptively changeable based on a detected breathing state.

12. The device of claim 10, wherein the smoothing criteria are selected from preset smoothing criteria for respective respiratory states.

13. The device of claim 1, wherein the at least one processor is further configured to compare the reference signal with at least a portion of the first signal received after the reference signal has been designated.

14. The device of claim 1, wherein the value of 1 is reached when the reference signal and the first signal exactly correspond to one another, and wherein the value of −1 is reached when the reference signal and the first signal are exactly opposed to one another.

15. A device for detecting a person's breathing activity and/or physiological condition, comprising:

a flow sensor configured to generate a first signal indicative of breathing gas flow over at least two breathing cycles; and

at least one processor configured to:

designate a limited portion of the first signal as a reference signal,

compare the reference signal with at least a portion of the first signal, and

generate, based on the comparison, an output signal indicative of the breathing activity and/or the physiological condition of the person,

wherein the portion of the first signal to which the reference signal is compared occurs prior to a time at which the reference signal is designated.

16. A device for detecting a person's breathing activity and/or physiological condition, comprising:

a flow sensor configured to generate a first signal indicative of breathing gas flow over at least two breathing cycles; and

at least one processor configured to:

monitor a second signal indicative of an amount of pressure provided to the person via a flow generator,

designate a limited portion of the first signal as a reference signal,

compare the reference signal with at least a portion of the first signal,

generate, based on the comparison, an output signal indicative of the breathing activity and/or the physiological condition of the person, and

mathematically correlate the reference signal with the first signal as the comparison,

wherein the mathematical correlation results in values between −1 and 1.

17. The device of claim 16, wherein the at least one processor is further configured to cause the flow generator to adjust the amount of pressure provided to the person in dependence on the output signal.

18. The device of claim 16, further comprising a filter configured to alter the first signal by removing or suppressing a predetermined frequency range therein.

19. The device of claim 16, further comprising a filter configured to alter the second signal by removing or suppressing a predetermined frequency range therein.

20. The device of claim 16, further comprising a filter configured to alter the first and second signals by removing or suppressing a predetermined frequency range therein.

21. The device of claim 16, wherein the at least one processor is further configured to identify snoring by detecting a increase in a variance of the second signal in one or more breathing cycles.

22. The device of claim 16, wherein the at least one processor is further configured to identify mouth breathing by detecting a negative correlation.

23. The device of claim 16, wherein the at least one processor is further configured to identify obstructive apneas by detecting a weakened and/or missing peak of correlation.

24. The device of claim 16, wherein the at least one processor is further configured to identify flow limited breathing by determining whether a maximum inspiration flow occurs within the first half of an inspiration cycle.

25. The device of claim 16, wherein the value of 1 is reached when the reference signal and the first signal exactly correspond to one another, and wherein the value of −1 is reached when the reference signal and the first signal are exactly opposed to one another.

26. A method for detecting a person's breathing activity and/or physiological condition, comprising:

generating a first signal indicative of breathing gas flow over at least two breathing cycles;

designating a limited portion of the first signal as a reference signal;

comparing the reference signal with at least a portion of the first signal; and

generating, based on the comparison, an output signal indicative of the breathing activity and/or the physiological condition of the person,

wherein the comparing comprises mathematically correlating the reference signal with the first signal, and

wherein the mathematical correlation results in values between −1 and 1.

27. The method of claim 26, further comprising determining whether a graph of the mathematical correlation in corresponding portions has a similar periodicity, and whether in the corresponding portions local maxima are close to 1 and local minima are close to −1, in order to determine whether successive breathing cycles are similar.

28. The method of claim 26, further comprising recognizing whether the person's respiration is regular.

29. The method of claim 26, further comprising recognizing whether the person's breaths are missed completely.

30. The method of claim 26, further comprising:

generating a signal corresponding to the first derivative of the first signal;

identifying local maxima and minima of the signal corresponding to the first derivative of the first signal;

recognizing transitions between inspiration and expiration with reference to the local maxima and minima; and

distinguishing between individual breathing phases in accordance with the recognized transitions.

31. The method of claim 26, further comprising causing a flow generator to adjust an amount of pressure provided to the person in dependence on the output signal.

32. The method of claim 26, wherein the first signal extends over at least three breathing cycles, and wherein the reference signal corresponds to at least two breathing cycles.

33. The method of claim 32, wherein the reference signal corresponds to exactly two breathing cycles.

34. The method of claim 26, further comprising removing or suppressing a predetermined frequency range in the first signal.

35. The method of claim 34, further comprising adaptively changing the smoothing criteria based on a detected breathing state.

36. The method of claim 26, further comprising smoothing the reference signal in accordance with smoothing criteria.

37. The method of claim 32, wherein the smoothing criteria are selected from preset smoothing criteria for respective respiratory states.

38. The method of claim 26, wherein the portion of the first signal to which the reference signal is compared occurs prior to a time at which the reference signal is designated.

39. The method of claim 26, wherein the comparing comprises comparing the reference signal with at least a portion of the first signal received after the reference signal has been designated.

40. The method of claim 26, wherein the value of 1 is reached when the reference signal and the first signal exactly correspond to one another, and wherein the value of −1 is reached when the reference signal and the first signal are exactly opposed to one another.

41. A method for detecting a person's breathing activity and/or physiological condition, the method comprising:

generating a first signal indicative of breathing gas flow over at least two breathing cycles;

monitoring a second signal indicative of an amount of pressure provided to the person via a flow generator;

designating a limited portion of the first signal as a reference signal;

comparing the reference signal with at least a portion of the first signal; and

generating, based on the comparison, an output signal indicative of the breathing activity and/or the physiological condition of the person,

wherein the mathematically comparing comprises mathematically correlating the reference signal with the first signal, and

wherein the mathematical correlation results in values between −1 and 1.

42. The method of claim 41, further comprising causing the flow generator to adjust the amount of pressure provided to the person in dependence on the output signal.

43. The method of claim 41, further comprising filtering the first signal by removing or suppressing a predetermined frequency range therein.

44. The method of claim 41, further comprising filtering the second signal by removing or suppressing a predetermined frequency range therein.

45. The method of claim 41, further comprising filtering the first and second signals by removing or suppressing a predetermined frequency range therein.

46. The method of claim 41, further comprising identifying snoring by detecting a increase in a variance of the second signal in one or more breathing cycles.

47. The method of claim 41, further comprising identifying mouth breathing by detecting a negative correlation.

48. The method of claim 41, further comprising identifying obstructive apneas by detecting a weakened and/or missing peak of correlation.

49. The method of claim 41, further comprising identifying flow limited breathing by determining whether a maximum inspiration flow occurs within the first half of an inspiration cycle.

50. The method of claim 41, wherein the value of 1 is reached when the reference signal and the first signal exactly correspond to one another, and wherein the value of −1 is reached when the reference signal and the first signal are exactly opposed to one another.